CN106443529A - Connection system and method - Google Patents
Connection system and method Download PDFInfo
- Publication number
- CN106443529A CN106443529A CN201610636047.6A CN201610636047A CN106443529A CN 106443529 A CN106443529 A CN 106443529A CN 201610636047 A CN201610636047 A CN 201610636047A CN 106443529 A CN106443529 A CN 106443529A
- Authority
- CN
- China
- Prior art keywords
- cable
- adapter
- connection system
- jack
- gradient coil
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
- G01R33/3858—Manufacture and installation of gradient coils, means for providing mechanical support to parts of the gradient-coil assembly
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R1/00—Details of instruments or arrangements of the types included in groups G01R5/00 - G01R13/00 and G01R31/00
- G01R1/02—General constructional details
- G01R1/04—Housings; Supporting members; Arrangements of terminals
- G01R1/0408—Test fixtures or contact fields; Connectors or connecting adaptors; Test clips; Test sockets
- G01R1/0416—Connectors, terminals
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
- G01R33/3854—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils means for active and/or passive vibration damping or acoustical noise suppression in gradient magnet coil systems
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F6/00—Superconducting magnets; Superconducting coils
- H01F6/06—Coils, e.g. winding, insulating, terminating or casing arrangements therefor
- H01F6/065—Feed-through bushings, terminals and joints
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01R—ELECTRICALLY-CONDUCTIVE CONNECTIONS; STRUCTURAL ASSOCIATIONS OF A PLURALITY OF MUTUALLY-INSULATED ELECTRICAL CONNECTING ELEMENTS; COUPLING DEVICES; CURRENT COLLECTORS
- H01R11/00—Individual connecting elements providing two or more spaced connecting locations for conductive members which are, or may be, thereby interconnected, e.g. end pieces for wires or cables supported by the wire or cable and having means for facilitating electrical connection to some other wire, terminal, or conductive member, blocks of binding posts
- H01R11/11—End pieces or tapping pieces for wires, supported by the wire and for facilitating electrical connection to some other wire, terminal or conductive member
- H01R11/30—End pieces held in contact by a magnet
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01R—ELECTRICALLY-CONDUCTIVE CONNECTIONS; STRUCTURAL ASSOCIATIONS OF A PLURALITY OF MUTUALLY-INSULATED ELECTRICAL CONNECTING ELEMENTS; COUPLING DEVICES; CURRENT COLLECTORS
- H01R9/00—Structural associations of a plurality of mutually-insulated electrical connecting elements, e.g. terminal strips or terminal blocks; Terminals or binding posts mounted upon a base or in a case; Bases therefor
- H01R9/03—Connectors arranged to contact a plurality of the conductors of a multiconductor cable, e.g. tapping connections
- H01R9/05—Connectors arranged to contact a plurality of the conductors of a multiconductor cable, e.g. tapping connections for coaxial cables
Abstract
A connection system includes a connector electrically connected and fixedly secured to a gradient coil assembly of a magnetic resonance imaging device, a cable block fixedly secured to a magnet of the magnetic resonance imaging device substantially above the connector, and a cable having a first end electrically connected to the cable block and a second end received by the connector and forming an electrical connection between the connector and the cable block.
Description
Technical field
Embodiments of the invention relate generally to nuclear magnetic resonance.Specific embodiment relates to secure connection cable to magnetic
The System and method for of the gradient coil of resonance image-forming equipment.
Background technology
Magnetic resonance system operated by coil for transmission have the high-frequency impulse that nuclear resounce excites and/or for
Receive the magnetic resonance signal of sensing.Typically, magnetic resonance system has：Superconducting coil, generates in inspection area preferably all
One basic magnetic field (B0)；Whole coil (also referred to as body coil), is installed in fixed position, applies typically horizontal stroke for of short duration
To in the pulsed RF magnetic field of B0（B1）；And multiple little surface coils（Also referred to as local coil）.Can be from it in order to obtain
Generate the information of patient image, the selection region of main body to be checked or patient passes through gradient coil for every in three axial directions
Individual read (for example, X, Y are about radial direction for patient, and Z is in the longitudinal direction of patient).Magnetic resonance x-ray tomography
Space encoding in art (tomography) is realized using gradient coil system, and this gradient coil system can with three
Independent control, magnetically orthogonal gradient field coil.Described gradient field coil can be jointly referred to as " gradient coil ".
By be superimposed these three can spread field (in X, tri- directions of Y, Z), the orientation of code plane (' gradient fields ') can
It is chosen freely.Typically, this gradient coil is spatially fixed on casting compound（casting compound）In,
And be allowed to be sealed in wherein.
High current must be supplied to gradient coil to generate gradient fields.Described electric current is hundreds of ampere；For example, 500-
The electric current of 1300 A is typical.In order to produce the connection of gradient coil, two plug element have been passed through in previous trial
（That is, plug and the mating connector detachably connectable with this plug）The high current that formed coaxially connected making.Described plug
On coaxial cable conductor to be connected, and supporting adapter (thus socket) is typically provided in gradient coil.For
Connect, in the mating connector that the plug positioned at coaxial cable end is inserted into gradient coil, and utilize hardware（Such as spiral shell
Mother and bolt or other screwed connection）It is fixed there.Many times, described connection may call for being torqued into and aligns
True setting.However, connect electric current carry cable and gradient coil such existing means may result in each plug element or
At the Plug contact of conductor side due to mechanical vibration and/or alternately electromagnetic force and so that cable is undesirably fallen off from gradient coil.In addition,
Using existing connection scheme, due to the property of used unit, cable typically extends axially away from gradient coil, and this requires line
Cable is then bent with generally an angle of 90 degrees, with the overall diameter past magnet.However, the specification of the given cable utilizing
When, this bending is not easy to.
In view of more than, exist and connect to the gradient of MR imaging apparatus for safely and reliably electric current being carried cable
The needs of the System and method for of coil.
Content of the invention
In one embodiment, a kind of connection system comprises：Adapter, is electrically connected and is fixedly secured（secure）To magnetic
The gradient coil assembly of resonance imaging device；Cable block, is generally fixedly secured to magnetic resonance above adapter
Magnet as device；And cable, there is the second end that the first end being electrically connected to cable block and connected device are received,
And form the electrical connection between described adapter and described cable block.
In another embodiment, a kind of method is provided.The method includes the steps of：Adapter is fixedly secured to
The gradient coil assembly of MR imaging apparatus, by the jack inserting from the plug of the cable that cable block extends in adapter to build
Vertical electrical connection therebetween, and terminal surface cable block being fixedly secured to the magnet of MR imaging apparatus.
In one embodiment, a kind of system is provided.This system comprises：Adapter, is filled（pot）Enter nuclear magnetic resonance dress
The gradient coil assembly put, this adapter has the jack being radially inwardly directed to；Cable block, is fixed typically above adapter
Be fastened to the magnet of MR imaging apparatus；And coaxial cable, downwardly depending from described cable block, and have in described company
Connect the plug being received in the jack of device.
Thus, the disclosure provides technical scheme below：
A kind of connection system of technical scheme 1., including：
Adapter, is electrically connected and is fixedly secured to the gradient coil assembly of MR imaging apparatus；
Cable block, is generally fixedly secured to the magnet of described MR imaging apparatus above described adapter；With
And
Cable, has the first end being electrically connected to described cable block and the second end being received by described adapter, and shape
Become the electrical connection between described adapter and described cable block.
Connection system as described in technical scheme 1 for the technical scheme 2., wherein：
Described adapter is loaded into described gradient coil assembly.
Connection system as described in technical scheme 2 for the technical scheme 3., wherein：
Second end of described cable comprises plug；And
Described adapter comprises the jack being configured to receive described plug.
Connection system as described in technical scheme 3 for the technical scheme 4., wherein：
Patient's receiver hole direction radially outwardly of the relatively described MR imaging apparatus of described jack.
Connection system as described in technical scheme 4 for the technical scheme 5., wherein：
Described cable is coaxial cable.
Connection system as described in technical scheme 5 for the technical scheme 6., wherein：
Described cable block has at least one terminal being configured to receive wire, and this wire is used for being electrically connected to described cable block
The gradient amplifier of described MR imaging apparatus.
Connection system as described in technical scheme 5 for the technical scheme 7., further includes：
Redundant physical between described cable and described adapter is connected.
Connection system as described in technical scheme 7 for the technical scheme 8., wherein：
Described redundancy link comprises the rotatable sleeve being integrated to form with described cable, described rotatable sleeve have be configured to use
In the flange being directly coupled to described adapter and gradient coil assembly.
Connection system as described in technical scheme 8 for the technical scheme 9., wherein：
Described flange is directly coupled to described adapter via at least one screw rod or cable ties.
Connection system as described in technical scheme 1 for the technical scheme 10., wherein：
The described jack of described adapter is oriented to the flange beyond described magnet.
A kind of method of technical scheme 11., comprises the following steps：
Adapter is fixedly secured to the gradient coil assembly of MR imaging apparatus；
The jack that will insert from the plug of the cable that cable block extends in described adapter, to set up electrical connection therebetween；And
Described cable block is fixedly secured to the terminal surface of the magnet of described MR imaging apparatus.
Method according to technical scheme 11 for the technical scheme 12., wherein：
The step being fixedly secured described adapter comprises to be oriented so that described jack in radial direction described adapter
Direction, beyond the flange of described magnet.
Method according to technical scheme 12 for the technical scheme 13., wherein：
The step being fixedly secured described adapter comprises for described adapter to load described gradient coil assembly.
Method according to technical scheme 13 for the technical scheme 14., further comprising the steps：
Set up the redundancy link between described cable and described adapter.
Method according to technical scheme 14 for the technical scheme 15., wherein：
The step setting up redundancy link comprises, via at least one of cable ties and screw rod, described cable is fastened to described company
Connect device.
Method according to technical scheme 12 for the technical scheme 16., wherein：
The described plug described jack of insertion is included in described plug band in the direction contrary with described radial direction to described
Jack.
Method according to technical scheme 11 for the technical scheme 17., wherein：
Described cable is coaxial cable.
Method according to technical scheme 11 for the technical scheme 18., further comprises the following steps：
Described cable block is electrically connected to the gradient amplifier of described MR imaging apparatus.
A kind of system of technical scheme 19., including：
Adapter, is loaded into the gradient coil assembly of MR imaging apparatus, and described adapter has the jack being radially inwardly directed to；
Cable block, is typically fixedly secured to the magnet of described MR imaging apparatus above described adapter；And
Coaxial cable, downwardly depending from described cable block, and there is the plug being received in the described jack of described adapter.
System as described in technical scheme 19 for the technical scheme 20., further includes：
The flange being integrated to form with described coaxial cable, described flange is secured to described adapter via fastening member, and carries
For the redundancy link between described cable and described adapter.
Brief description
From the subsequent description that non-limiting example is read with reference to the drawings, the present invention will be better understood when, wherein exists
Below:
Fig. 1 schematically shows exemplary nuclear magnetic resonance (MRI) system, and it combines embodiments of the invention.
Fig. 2 is the end view of the magnetic resonance imaging system of Fig. 1, illustrates gradient line astragal according to an embodiment of the invention
Cable connection system.
Fig. 3 is the detail perspective view of the axial end of the magnetic resonance imaging system of Fig. 1, illustrates that gradient coil cable connects system
System.
Fig. 4 is the detail perspective view of the axial end of the magnetic resonance imaging system of Fig. 1, illustrates described gradient coil cable even
The adapter of welding system.
Fig. 5 is the details end view of the magnetic resonance imaging system of Fig. 1, illustrates described adapter.
Specific embodiment
In detail reference is carried out to the one exemplary embodiment of the present invention below, its example is demonstrated in the accompanying drawings.In office
In place of what is possible, refers to identical or similar part throughout the same reference character that in figure is used, and need not repeat
Bright.Although the one exemplary embodiment of the present invention is to carry conductor to the connection of the gradient coil of magnetic resonance imaging system for electric current
Come to describe, embodiments of the invention can also be generally applicable to the use in MRI system, and the company of being generally applicable to
Connect.
As used herein, term " generally (substantially) ", " general (generally) ", and " big
About (about) " instruction manufactures and component tolerances reasonably accessibility（tolerance）Interior situation（With respect to suitable
Reach the ideal expectation situation of the function and usage of part or assembly）.As used herein, term " electrical connection
(electrically connected) ", " telecommunication（electrical communication）" or " electric coupling
(electrically coupled) " means that the element quoted directly or indirectly is connected so that electric current can be from one
Flow to another.Described connection can comprise directly to conduct connection (that is, does not have electric capacity, the sensing or active intervening
（active）Element), sensing connect, capacitance connection and/or any other suitable electrical connection.Intervention part there may be.
Fig. 1 illustrates the critical piece of exemplary nuclear magnetic resonance (MRI) system 10 combining the embodiment of the present invention.Institute
The operation stating system to control from operator's console 12, and this control station comprises：Keyboard or other input equipment 13, control plane
14 and display screen 16.Described input equipment 13 can comprise：Mouse, stick, keyboard, tracking ball, touch activation screen
Curtain, optical wand（light wand）, sound control or any similar or equivalent input equipment, and can be used for interacting geometry rule
Fixed（prescription）.Control station 12 is communicated with detached computer system 20 by link 18, this computer system
Enable the operator to control the generation of image and the display on display screen 16.Described computer system 20 comprises the bottom of by
Plate 20a and the multiple modules communicating with one another.
The module of computer system 20 comprises：Image processor block 22, CPU module 24 and memory module 26, deposit
Memory modules 26 can comprise the frame buffer for storage image data array.Computer system 20 is linked to archives media dress
Put, permanent or backup of memory storage device（memory storage）Or network depositing for view data and program
Storage, and control 32 to be communicated by the signal link 34 of high speed and detached MRI system.Computer system 20 and MRI system
System controls 32 to be collectively form " MRI controller " 33.
MRI system controls the set of 32 modules comprising to be linked together by base plate 32a.These modules comprise CPU module
36 and impulse generator module 38.Described CPU module 36 is connected to operator's console 12 by data link 40.Exactly logical
Cross link 40, MRI system controls 32 to receive the order from the instruction of operator scanning sequence to be executed.CPU module 36 is grasped
To execute desired scanning sequence as system unit, and produce the sequential of RF pulse, intensity and shape produced by instruction and
The sequential of data acquisition window and the data of length.If described CPU module 36 connects to the cadre operated by MRI Controller 33
Part, comprises：Impulse generator module 38（It controls gradient amplifier 42, is discussed further below）, physiological acquisition controller
（“PAC”）44 and scan room interface circuit 46.
Described CPU module 36 receives the patient data coming from physiological acquisition controller 44, and this controller receives and comes from
The signal of the multiple different sensors being connected with patient, for example, come from the ECG signal of the electrode being attached to patient.And
Eventually, described CPU module 36 receives and comes from scan room interface circuit 46, and comes from the situation phase with magnet system and patient
The signal of the various sensors of association.Also it is exactly based on scan room interface circuit 46, MRI Controller 33 order patient positioning system
48 mobile patients or client C are to desired locations to scan.
The expectation of the gradient pulse that impulse generator module 38 operates gradient amplifier 42 to realize being generated during scanning
Sequential and shape.Gradient waveform produced by impulse generator module 38 is applied in gradient amplifier system 42, and this is
System has Gx, Gy and Gz amplifier.Each gradient amplifier excites gradient coil assembly（Generally it is designated as 50）In
Corresponding physics gradient coil, to produce the magnetic field gradient signal collected for space encoding.Gradient coil assembly 50 defines
The part of magnet assembly 52, assembly 52 also comprises polarized magnets 54（In operation, it provides homogeneous longitudinal magnetic field B0, this magnetic field
Throughout the target volume area being surrounded by magnet assembly 52（volume）55）And entirety（Transmission and reception）RF coil 56（In behaviour
In work, it provides the transverse magnetic field B1 being generally perpendicular to B0 throughout target volume area 55）.As shown in fig. 1, gradient amplifier
42 are electrically connected to gradient coil assembly 50 via one or more cables 53.The connection system being discussed below provide cable 53 with
Physical interconnections between gradient coil assembly 50.RF coil 56 encloses target volume area and defines general shape in a tubular form
Patient's receiver hole 59.
MRI machine 10 also comprises surface（Receive）Coil 57, it can be single channel or multichannel.MRI system controls 32
In transceiver module 58 produce pulse, these pulses are amplified by RF amplifier 60 and are passed through transmission/receive switch and 62 are coupled
To RF coil 56.Can be by identical RF coil 56 and by special reception line by the signal exciting obtained by nuclear emission in patient
Circle 57 is sensed, and is coupled to preamplifier 64 by transmission/reception switch 62.The MR signal amplifying is in transceiver 58
Receptor partly in demodulated, filtration and digitized.Transmission/reception switch 62 is come from impulse generator module 32
Signal is controlled, RF amplifier 60 to be electrically connected to coil 56 during transfer mode, and will be preposition during reception pattern
Amplifier 64 connects to coil 56.Described transmission/reception switch 62 also can enable surface RF coils 57 be used in or pass
Send in pattern or reception pattern.
After multi-channel RF coil 56 and/or surface coils 57 have picked up and have excited the RF signal of generation from target, transceiver
Module 58 is by these signal digitizeds.Then MRI Controller 33 passes through these digitized signals of Fourier transform processing, to produce
Raw k-space data, then this data controls 32 to be passed to memory module 66 or other computer-readable via MRI system
Media." computer-readable media " can comprise, and for example, is arranged so that electricity, light or magnetic state can be able to be perceived with conventional computer
And reproducible mode is come the structure to fix：For example, be printed onto paper or be shown in text on screen or image, CD or
Other optical storage medias；" flash " memorizer, EEPROM, SDRAM or other electricity storage media；Floppy disk or other disk, magnetic
Band or other magnetic recording medium.
When original k-space data array has been collected in computer-readable media 66, scanning just completes.This
Plant original k-space data and be rearranged into detached k-space data array for each image to be reconstructed, and these numbers
Each according to array is input to array processor 68, and its operation to become the array of view data by data Fourier transform.This
Plant view data and computer system 20 is communicated to by data link 34, there it is stored in memorizer.Response from
The order that operator's console 12 receives, view data can be archived in long-term storage apparatus, or it can be by image
Processor 22 processes further and is communicated to operator's console 12, and shows on the display 16.
Referring now to Fig. 2-5, illustrate for connecting gradient coil cable 53 to the connection system of gradient coil assembly 50
100.Described connection system 100 comprises adapter 102, and it has the jack being electrically coupled to gradient coil assembly 50
（receptacle）104.In one embodiment, described jack 104 is co-axial cable jack, and it is configured to receive coaxial cable
Insert ends, just as discussed in detail below.As best shown in Fig. 4 and Fig. 5, adapter 102 is loaded into or otherwise
It is charged（impregnate）In gradient coil assembly 50（Carry leaded to therein gradient coil）In, and be oriented such that
Jack 104 from patient's receiver hole 59 radially outwardly towards and extend beyond magnet flange.When using herein, " radially
Direction " means that patient's receiver hole relatively is oriented radially, and is generally orthogonal to the longitudinal axiss in this hole.In an embodiment
In, adapter 102 is loaded in gradient coil assembly 50 so that jack 50 direction directly up.In one embodiment, adapter
102 shell（housing）It is fireproof.
In other embodiments, for example wherein magnet is longer than gradient coil assembly 50, and adapter 102 can be loaded into ladder
Degree coil block 50 so that jack 104 axially towards.In any embodiment, adapter 102 is fixedly secured to gradient
Coil block 50.In one embodiment, the height of adapter 102 is less than the height of existing adapter, this removes generally
The pack clearance problem existing.Particularly, the reduction of adapter 102 highly allows jack 104 direction radially up, rather than
Axially.
Specifically with reference to Fig. 4 and Fig. 5, connection system 100 also comprises have chlamydate cable block 106, and from this shell
The flexible coaxial cable 108 extending.Described cable 108 has the first end being electrically connected to cable block 106 and terminates at plug
The second end in 110, this plug is adjusted size and shape, so that the jack 104 being connected in device 102 is received, thus
Set up electrical connection therebetween.Rotatable sleeve（boot）112 enclose plug 110, and are rotatable with respect to cable 108.
Described sleeve pipe 112 provides the redundancy link between cable block 106 and adapter 102, just as discussed in detail below.Real one
Apply in example, coaxial cable 108 is designed to process the electric current more than 1000 Amp and 450 Arm.
Also as shown in Figure 4 and Figure 5, cable block 106 comprises the multiple electric terminals 114 being electrically connected to coaxial cable 108, these
Electric terminal allows for cable 108 via couple of conductor（For example, gradient coil cable 53）Connect to gradient amplifier 42.Example
As terminal 114 can comprise to be electrically connected to the M10 nail of coaxial cable 108 center conductor（stud）, and it is electrically connected to coaxial line
Two M10 nails of cable 108 shielded conductor, for receiving the gradient coil cable 53 stretching to gradient amplifier 42.Nail
This configuration prevents the accident of the positive and negative wire stretching to gradient amplifier 42 to change, and provides the ground connection of magnet.
As best shown in Fig. 4 and Fig. 5, in one example, cable block 106 is fixedly attached to screw rod or other fastener
The end of magnet 54, is located immediately at the top of adapter 102, coaxial cable 108 from cable block 106 downwardly depending so that plug
110 can be inserted into jack 104 from above.This arrangement minimizes technical staff and improperly connection is wired to gradient line
The ability of circle, as discussed below.In fact, when connected, cable 108 exits from straight from jack 104, and this disappears
Except bending cable 108 so that it be placed in magnetic field in addition to demand, as discussed below.
In use, adapter 102 is loaded into gradient coil assembly 50 so that jack 104 is oriented radially and substantially
On upwardly toward.Then the insert ends 110 of coaxial cable 108 can be inserted jack 104 from top by technical staff, to set up
Electrical connection therebetween, and do not use torque wrench and hardware.Then cable block 106 is fixedly mounted with screw rod or other fastener
End to magnet 54（For example, to magnet flange）.In one embodiment, the clip that spring loads can be used to stop screw rod
Poured out due to vibrations（back out）.
The end that cable block 106 is fixedly installed to magnet 54 forces coaxial cable 108 and the comfortable reliability of its plug 110
Stay in adapter 102 jack 104 inside.Particularly, in one embodiment, plug 110 must vertically move about
1.5 inches being disconnected.Using by M10 nail（Via cable block 106）It is bolted to the opposing end portions of the cable 108 of magnet,
And using stiff coaxial cable, connection is nature occlusion.By cable be suppressed to magnet flange actually prevent cable from
Jack departs from.
As mentioned, the sleeve pipe 112 on cable 108 provide superfluous between cable block 106 and adapter 102
Remaining connection.Particularly, in one embodiment, sleeve pipe 112 comprises the flange wherein with multiple holes.Can be using screw rod by sleeve pipe
112 and thus coaxial cable 108 is redundantly secured directly to adapter 102.In other embodiments, zip knot（zip
tie）Or cable ties can be utilized to for sleeve pipe 112 to be secured directly to adapter 102.In the more extensive areas without departing from the present invention
In the case of, other fixing means can also be utilized.In one embodiment, described sleeve pipe and plug mould（overmold）Can
To manufacture from flame retardant materials.Flame retardant materials prevent any thing of other on any arc ignition magnet or patient space
Body, and thus provide extra safe floor.Once the connection between cable block 106 and adapter 102 is arrived via plug 110 and is inserted
Insertion in seat and be established, and cable block 106 is fixedly secured to the magnet of jack 104 top it is possible to will be from ladder
Couple of conductor that degree amplifier 42 extends（For example, cable 53）Connect the terminal 114 to cable block 106.
Connection system 100 is thus provided that and is safely and reliably electrically connected between gradient amplifier 42 and gradient coil assembly 50
Connect.As discussed above, existing System and method for is coaxial by stretch out from gradient amplifier typically with the contact tacking
Cable is connected to gradient coil assembly, and this requires assembly to be rotated to accurate setting, to guarantee reliably to connect.However, with
Compared with method, the connection system 100 of the present invention make use of the adapter being directly charged into gradient coil assembly 50 to existing system
102, eliminate the needs using the connection tacked therebetween.Additionally, simple plug is connected with socket providing in this area so far
The present do not met assembly just.
In addition, existing system and method are typically with the coaxial cable axially outwardly extending from gradient coil assembly, should
Cable is bent with an angle of 90 degrees then up, so that cable is positioned to the overall diameter beyond magnet and thus outer in magnetic field
Face.However, coaxial cable is very thick and is difficult to be bent, particularly in short length, this can choose to bringing during installation
Fight and tension force can be placed on cable.The present invention passes through for adapter 102 to be oriented so that its jack 104 outwardly and upwardly
Radially rather than axially towards, eliminate bending coaxial cable needs.Correspondingly, coaxial cable 108 can be from top quilt
Insertion jack 104, eliminates bending cable so that it is placed in the needs outside the overall diameter of magnet.Correspondingly, this configuration
Cable 108 is allowed to extend directly up with straight line, in order to install.
As artisan will readily appreciate that, adapter 102 is fixedly secured to gradient coil assembly 50, and by adapter
Block 106 is fixedly secured to the end of magnet, provides two fixing points, it plays on the opposing end portions of coaxial cable 108
By connecting between plug 110 and jack 104 and the vibrations that electrically connect therebetween or other motion isolation can be negatively affected
Effect.Particularly, this two fixing points stops vibrations or similar motion from traveling to plug and be connected with jack, and prevention would generally
The tension force on cable 108 that caused by this vibrations or cable 108 are with respect to the distortion of adapter 102.In fact, this two solid
Fixed point inhibits cable 108 to disconnect from jack 104.As a result, safely and reliably connect and can be implemented.In addition, via screw rod
Or sleeve pipe 112 is directly fastened to the connection that adapter 102 provides redundancy by similar component, it has ensured reliability further,
And stop cable 108 from becoming to disconnect from adapter 102.
In addition to the above, generally speaking, provide, using the short coaxial cable of length 108, the cost reducing.With above institute
State correlation, in magnetic field, coaxial connector 102 and coaxial cable 108 internally and external concentric cable between naturally
Stress balance, because positive current is by negative electricity mobile equilibrium in identical cable.Correspondingly, the resulting net force in cable is zero, and this removes can
The potential motor connecting can be endangered.
In one embodiment, a kind of connection system comprises：Adapter, is electrically connected and is fixedly secured to nuclear magnetic resonance
The gradient coil assembly of device；Cable block, is generally fixedly secured to nuclear magnetic resonance dress above described adapter
The magnet put；And cable, there is the second end that the first end being electrically connected to cable block and connected device are received, and shape
Become the electrical connection between adapter and cable block.In one embodiment, adapter is loaded into gradient coil assembly.In an embodiment
In, the second end of cable comprises plug, and adapter comprises to be configured to receive the jack of this plug.In one embodiment, insert
Hole is relative to patient's receiver hole direction radially outwardly of MR imaging apparatus.In one embodiment, cable is coaxial cable.?
In one embodiment, cable block can have at least one terminal being configured to receive wire, and this wire is used for electrically connecting cable block
Gradient amplifier to MR imaging apparatus.In one embodiment, this system also comprises the redundancy between cable and adapter
Connect.This redundancy link can comprise the rotatable sleeve being integrated to form with cable.This rotatable sleeve have be disposed for straight
Connect the flange being coupled to adapter.In one embodiment, this flange is directly coupled to adapter via at least one screw rod.?
In one embodiment, the jack of adapter is positioned beyond the flange of magnet.
In one embodiment, a kind of method comprises the steps of：Adapter is fixedly secured to MR imaging apparatus
Gradient coil assembly, by the jack inserting from the plug of the cable that cable block extends in adapter to set up being electrically connected therebetween
Connect, and cable block is fixedly secured to the terminal surface of the magnet of MR imaging apparatus.In one embodiment, regularly tightly
The step being solidly connected device comprises adapter to be oriented so that jack direction in radial direction, beyond the flange of magnet.One
In embodiment, the step being fixedly secured adapter comprises for adapter to load gradient coil assembly.In one embodiment, the party
Method also can comprise the step setting up the redundancy link between cable and adapter.In one embodiment, the method can comprise to set up
The step of redundancy link comprises, via at least one of zip knot and screw rod, cable is fastened to adapter.In an embodiment
In, the step that plug is inserted jack is included in plug band in the direction contrary with radial direction to jack.In an embodiment
In, cable is coaxial cable.In one embodiment, the method also can comprise for cable block to be electrically connected to MR imaging apparatus
The step of gradient amplifier.
In one embodiment, a kind of system is provided.This system comprises：Adapter, is loaded into MR imaging apparatus
Gradient coil assembly, this adapter has the jack being radially inwardly directed to；Cable block, by regularly tight typically above adapter
It is affixed to the magnet of MR imaging apparatus；And coaxial cable, downwardly depending from cable block, and have in the jack of adapter
The plug being received.In one embodiment, this system also comprises the flange being integrated to form with coaxial cable, and this flange is via fastening
Component is secured to adapter, and provides the redundancy link between cable and adapter.
To be appreciated that, above description is intended to illustrative, and is not restricted.For example, described above
Embodiment（And/or its aspect）Can with used in combination with each other.In addition, without departing from the scope of the invention, perhaps
Many modifications can be made, so that particular condition or material are adapted to the teachings of the present invention.Although material described herein
Size and species be intended to define the parameter of the present invention, but they are by no means limitative, and are one exemplary embodiment.?
When checking above description, many other embodiments will be apparent from for those skilled in the art.Therefore, this
The four corner of the equivalents that bright scope should be authorized to together with such claim with reference to appended claims to determine.
In the appended claims, term " comprises（including）" and " wherein（in which）" it is used as corresponding term " bag
Include（comprising）" and " wherein（wherein）" plain English（plain-English）Equivalents.Additionally, following
In claim, the such as term such as " first ", " second ", " the 3rd ", " upper ", " lower ", " bottom ", " top "
It is only used as label to use, and be not intended to digital or position requirement is applied on their object.Additionally, the power followed
The restriction that profit requires is not to be write with the form of means-plus-function, and is not intended to based on 35U.S.C.112 the 6th sections are come
Explained, unless and until such claim limits, and clearly using phrase, " means are used for（means for）", and be followed by
With the function statement without further structure.
This written description uses examples to disclose some embodiments of the present invention, comprises optimal mode, and also makes ability
Those of ordinary skill in domain can put into practice embodiments of the invention, comprises to make and using any device or system and hold
The method of any combination of row.The patentable scope of the present invention is defined by the claims, and can comprise this area
In the other examples expected of those of ordinary skill.If they have not different from the literal language of claim structural elements
Part, or if they comprise the equivalent structural elements having non-intrinsically safe difference with the literal language of claim, then such other
Example is intended within the scope of claim.
As used herein, it is described with odd number and continue with word "（A or an）" element or step should be managed
Solve as being not excluded for multiple described elements or step, unless such exclusion is clearly stated.Additionally, " the reality to the present invention
Apply example " reference be not intended to be interpreted exclude the presence also in relation with the additional embodiment being described feature.Additionally, unless
Clearly carry out phase counterstatement, " include（comprising）", " comprise（including）" or " have（having）" there is spy
The embodiment of one element of qualitative matter or multiple element can comprise this other class component without that property.
Due in the case of the spirit and scope without departing from the described invention involved by this paper, can be described above
Method and apparatus in make some changes, so all themes being illustrated in described above or accompanying drawing are intended to be explained
For being intended only as example, inventive concepts herein to be described, and to be not necessarily to be construed as limiting the present invention.
Claims (10)
1. a kind of connection system（100）, including：
Adapter（102）, it is electrically connected and be fixedly secured to MR imaging apparatus（10）Gradient coil assembly（50）；
Cable block（106）, generally in described adapter（102）Top be fixedly secured to described MR imaging apparatus
（10）Magnet（54）；And
Cable（108）, have and be electrically connected to described cable block（106）First end and by described adapter（102）Received
The second end, and form described adapter（102）With described cable block（106）Between electrical connection.
2. connection system as claimed in claim 1（100）, wherein：
Described adapter（102）It is loaded into described gradient coil assembly（50）.
3. connection system as claimed in claim 2（100）, wherein：
Described cable（108）The second end comprise plug（110）；And
Described adapter（102）Comprise to be configured to receive described plug（110）Jack（104）.
4. connection system as claimed in claim 3（100）, wherein：
Described jack is with respect to described MR imaging apparatus（10）Patient's receiver hole（59）Direction radially outwardly.
5. connection system as claimed in claim 4（100）, wherein：
Described cable（108）For coaxial cable.
6. connection system as claimed in claim 5（100）, wherein：
Described cable block（106）There is at least one terminal being configured to receive wire（114）, described wire is used for described line
Cable block（106）It is electrically connected to described MR imaging apparatus（10）Gradient amplifier（42）.
7. connection system as claimed in claim 5（100）, further include：
Described cable and described adapter（102）Between redundant physical connect.
8. connection system as claimed in claim 7（100）, wherein：
Described redundancy link comprises：With described cable（108）The rotatable sleeve being integrated to form（112）, described rotatable sleeve
（112）Have and be configured to be directly coupled to described adapter（102）With described gradient coil assembly（50）Flange.
9. connection system as claimed in claim 8（100）, wherein：
Described flange is directly coupled to described adapter via at least one screw rod or cable ties（102）.
10. connection system as claimed in claim 1（100）, wherein：
Described adapter（102）Described jack be oriented to beyond described magnet（54）Flange.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US14/820,918 US10114092B2 (en) | 2015-08-07 | 2015-08-07 | Connection system and method |
| US14/820918 | 2015-08-07 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN106443529A true CN106443529A (en) | 2017-02-22 |
| CN106443529B CN106443529B (en) | 2021-02-05 |
Family
ID=56936570
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201610636047.6A Active CN106443529B (en) | 2015-08-07 | 2016-08-05 | Connection system and method |
Country Status (4)
| Country | Link |
|---|---|
| US (1) | US10114092B2 (en) |
| KR (1) | KR102541723B1 (en) |
| CN (1) | CN106443529B (en) |
| GB (1) | GB2541541B (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112578324A (en) * | 2019-09-29 | 2021-03-30 | 西门子(深圳)磁共振有限公司 | Gradient coil assembly and magnetic resonance imaging system |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| USD840540S1 (en) * | 2016-11-23 | 2019-02-12 | General Electric Company | Connector for a medical imaging device |
Citations (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0638814B1 (en) * | 1993-08-09 | 1998-02-04 | Picker International, Inc. | Magnetic resonance systems |
| JP2002085370A (en) * | 2000-09-13 | 2002-03-26 | Toshiba Corp | Magnetic resonance imaging apparatus |
| JP3367685B2 (en) * | 1992-05-20 | 2003-01-14 | 株式会社東芝 | Cable processing apparatus and magnetic resonance imaging apparatus having the same |
| CN2535950Y (en) * | 2002-04-03 | 2003-02-12 | 哈尔滨铁路局通信信号技术开发公司 | Interconnecting cable box of electric switch and connecting device therebetween |
| CN101405608A (en) * | 2006-03-17 | 2009-04-08 | 3M创新有限公司 | Test connector, kit and method for distinguishing a group of wires from other wires of a multi-wire cable |
| CN101854039A (en) * | 2009-03-30 | 2010-10-06 | 矢崎总业株式会社 | Motor cable assembly and method of manufacturing cable main body of the same |
| CN202111117U (en) * | 2011-05-05 | 2012-01-11 | 泰科电子(上海)有限公司 | Wiring module for solar panels |
| CN102565731A (en) * | 2010-11-24 | 2012-07-11 | 西门子公司 | Spine coil unit |
| CN102918718A (en) * | 2010-05-10 | 2013-02-06 | 罗森伯格高频技术有限及两合公司 | Electrical connection system |
| CN203631862U (en) * | 2013-11-06 | 2014-06-04 | 北京机电工程研究所 | Separating, pressing and pulling mechanism |
| CN103941202A (en) * | 2013-01-22 | 2014-07-23 | 上海联影医疗科技有限公司 | Shoulder coil used for magnetic resonance imaging equipment |
| CN104455825A (en) * | 2013-09-13 | 2015-03-25 | 诺信公司 | Quick connect fluid conduit connector having latch with integral spring arms for button release |
| US9241765B2 (en) * | 2003-09-30 | 2016-01-26 | Invivo Corporation | Open architecture imaging apparatus and coil system for magnetic resonance imaging |
Family Cites Families (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6954068B1 (en) | 2000-01-21 | 2005-10-11 | Kabushiki Kaisha Toshiba | Magnetic resonance imaging apparatus |
| DE102007007541A1 (en) | 2007-02-15 | 2008-08-21 | Siemens Ag | High-current coaxial connection with two connectable plug-in elements as well as gradient coil with connected high-current coaxial cable |
| DE102007059521B4 (en) | 2007-12-11 | 2016-11-17 | Siemens Healthcare Gmbh | High-current coaxial connection with two connectable plug-in elements as well as gradient coil with connected high-current coaxial cable |
| DE102009036233B4 (en) | 2009-08-05 | 2012-11-29 | Siemens Aktiengesellschaft | Loosening lock for coaxial gradient coil connections |
| DE102009036182B4 (en) | 2009-08-05 | 2013-09-19 | Siemens Aktiengesellschaft | Loosening lock for gradient coil connections |
| US8735723B2 (en) | 2010-11-15 | 2014-05-27 | General Electric Company | Apparatus and method for providing electric cables within a magnetic resonance imaging system |
| DE102011084021B4 (en) | 2011-10-05 | 2015-04-02 | Siemens Aktiengesellschaft | Connecting device for a magnetic system of an imaging system |
| DE102012216303A1 (en) * | 2012-09-13 | 2014-03-13 | Siemens Aktiengesellschaft | Magnetic resonance recording unit and a magnetic resonance device with the magnetic resonance recording unit |
| KR101600886B1 (en) * | 2013-12-17 | 2016-03-09 | 삼성전자주식회사 | Magnetic resonance imaging apparatus |
| KR101652047B1 (en) * | 2014-12-04 | 2016-08-29 | 삼성전자주식회사 | Magnetic resonance imaging apparatus and method thereof |
| CN205120950U (en) | 2015-10-30 | 2016-03-30 | 上海联影医疗科技有限公司 | Gradient coil termination and magnetic resonance system |
-
2015
- 2015-08-07 US US14/820,918 patent/US10114092B2/en active Active
-
2016
- 2016-07-28 GB GB1613049.4A patent/GB2541541B/en active Active
- 2016-08-01 KR KR1020160097920A patent/KR102541723B1/en active IP Right Grant
- 2016-08-05 CN CN201610636047.6A patent/CN106443529B/en active Active
Patent Citations (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP3367685B2 (en) * | 1992-05-20 | 2003-01-14 | 株式会社東芝 | Cable processing apparatus and magnetic resonance imaging apparatus having the same |
| EP0638814B1 (en) * | 1993-08-09 | 1998-02-04 | Picker International, Inc. | Magnetic resonance systems |
| JP2002085370A (en) * | 2000-09-13 | 2002-03-26 | Toshiba Corp | Magnetic resonance imaging apparatus |
| CN2535950Y (en) * | 2002-04-03 | 2003-02-12 | 哈尔滨铁路局通信信号技术开发公司 | Interconnecting cable box of electric switch and connecting device therebetween |
| US9241765B2 (en) * | 2003-09-30 | 2016-01-26 | Invivo Corporation | Open architecture imaging apparatus and coil system for magnetic resonance imaging |
| CN101405608A (en) * | 2006-03-17 | 2009-04-08 | 3M创新有限公司 | Test connector, kit and method for distinguishing a group of wires from other wires of a multi-wire cable |
| CN101854039A (en) * | 2009-03-30 | 2010-10-06 | 矢崎总业株式会社 | Motor cable assembly and method of manufacturing cable main body of the same |
| CN102918718A (en) * | 2010-05-10 | 2013-02-06 | 罗森伯格高频技术有限及两合公司 | Electrical connection system |
| CN102565731A (en) * | 2010-11-24 | 2012-07-11 | 西门子公司 | Spine coil unit |
| CN202111117U (en) * | 2011-05-05 | 2012-01-11 | 泰科电子(上海)有限公司 | Wiring module for solar panels |
| CN103941202A (en) * | 2013-01-22 | 2014-07-23 | 上海联影医疗科技有限公司 | Shoulder coil used for magnetic resonance imaging equipment |
| CN104455825A (en) * | 2013-09-13 | 2015-03-25 | 诺信公司 | Quick connect fluid conduit connector having latch with integral spring arms for button release |
| CN203631862U (en) * | 2013-11-06 | 2014-06-04 | 北京机电工程研究所 | Separating, pressing and pulling mechanism |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112578324A (en) * | 2019-09-29 | 2021-03-30 | 西门子(深圳)磁共振有限公司 | Gradient coil assembly and magnetic resonance imaging system |
| CN112578324B (en) * | 2019-09-29 | 2024-03-19 | 西门子(深圳)磁共振有限公司 | Gradient coil assembly and magnetic resonance imaging system |
Also Published As
| Publication number | Publication date |
|---|---|
| GB2541541A (en) | 2017-02-22 |
| KR20170017742A (en) | 2017-02-15 |
| CN106443529B (en) | 2021-02-05 |
| GB2541541B (en) | 2018-10-10 |
| US10114092B2 (en) | 2018-10-30 |
| GB201613049D0 (en) | 2016-09-14 |
| US20170038445A1 (en) | 2017-02-09 |
| KR102541723B1 (en) | 2023-06-08 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US8035384B2 (en) | Hybrid birdcage-TEM radio frequency (RF) coil for multinuclear MRI/MRS | |
| JP4977451B2 (en) | Cold mass with discrete paths and substantially conductive couplers for superconducting magnets and refrigerant cooling circuits | |
| US8890529B2 (en) | System and apparatus for providing interconnections in a gradient coil assembly | |
| US7161353B2 (en) | Magnetic resonance tomograph with an insertable gradient coil and a bundled detachably coupled water and electrical supply line | |
| US7414401B1 (en) | System and method for shielded dynamic shimming in an MRI scanner | |
| US9810755B2 (en) | System and method for energizing a superconducting magnet | |
| US20100060282A1 (en) | Three-dimensional asymmetric transverse gradient coils | |
| JP5068586B2 (en) | Method and apparatus for locally shielding MR superconducting magnet coils | |
| US8373417B2 (en) | Method and device to detect failure of a magnetic resonance gradient coil by monitoring a supply cable thereof | |
| GB2476546A (en) | Structural support member allowing alignment adjustment between coil formers in a magnet system | |
| CN106443529A (en) | Connection system and method | |
| CN102058410A (en) | Integrated electronic RF shielding apparatus for an MRI magnet | |
| US20140184226A1 (en) | System and apparatus for active high order shimming | |
| JP6061518B2 (en) | System and apparatus for balancing radial forces in gradient coils | |
| US20140184222A1 (en) | Matrix shim coil apparatus | |
| US20170123026A1 (en) | Magnetic resonance imaging matrix shim coil system and method | |
| US8471561B2 (en) | Safeguard for unscrewing gradient coil connections | |
| CN103675732A (en) | Combined HF/Shim/Gradient Signal Routing | |
| JP6288960B2 (en) | Magnetic resonance imaging system | |
| US10156620B2 (en) | Multifunctional superconducting coil providing electromagnetic interference shielding and shimming for magnetic resonance imaging system | |
| US7019525B2 (en) | Method and apparatus for magnetic resonance imaging | |
| JP2005044826A (en) | Magnetic canceler |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |